Hybrid stent

ABSTRACT

A stent includes a high radial force segment and a highly flexible segment, where the diameters of the high radial force segment and the highly flexible segment are substantially the same. The stent may further be placed with an additional stent segment, where the additional stent segment has a radial force similar to the radial force of the highly flexible force segment.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No. 16/799,233, filed Feb. 24, 2020, pending, which is a continuation of U.S. patent application Ser. No. 16/397,085 filed Apr. 29, 2019, now U.S. Pat. No. 10,588,764, which is a divisional of U.S. patent application Ser. No. 15/712,704 filed Sep. 22, 2017, now U.S. Pat. No. 10,271,977, which claims the benefit of priority to U.S. Provisional Patent Application No. 62/555,894 filed Sep. 8, 2017, the disclosures of which are incorporated herein by reference in its entirety.

BACKGROUND Field of the Invention

Disclosed herein are stents for implantation within the body and methods for delivery and/or deployment. Certain embodiments disclosed herein may be used in procedures to treat May-Thurner syndrome and/or deep venous thrombosis and the resulting post-thrombotic syndrome.

Description of the Related Art

May-Thurner syndrome, also known as iliac vein compression syndrome, is a condition in which compression of the common venous outflow tract of the left lower extremity may cause various adverse effects, including, but not limited to, discomfort, swelling, pain, and/or deep venous thrombosis (DVT) (commonly known as blood clots). May-Thurner syndrome occurs when the left common iliac vein is compressed by the overlying right common iliac artery, leading to stasis of blood, which may cause the formation of blood clots in some individuals. Other, less common, variations of May-Thurner syndrome have been described, such as compression of the right common iliac vein by the right common iliac artery.

While May-Thurner syndrome is thought to represent between two to five percent of lower-extremity venous disorders, it frequently goes unrecognized. Nevertheless, it is generally accepted that May-Thurner syndrome is about three times more common in women than it is in men and typically manifests itself between the age of twenty and forty. Patients exhibiting both hypercoagulability and left lower extremity thrombosis may be suffering from May-Thurner syndrome. To confirm that diagnosis, it may be necessary to rule out other causes for hypercoagulable state, for example by evaluating levels of antithrombin, protein C, protein S, factor V Leiden, and prothrombin G20210A.

By contrast to the right common iliac vein, which ascends almost vertically parallel to the inferior vena cava, the left common iliac vein takes a more transverse course. Along this course, it lies under the right common iliac artery, which may compress it against the lumbar spine. Iliac vein compression is a frequent anatomic variant—it is thought that as much as 50% luminal compression of the left iliac vein occurs in a quarter of healthy individuals. However, compression of the left common iliac vein becomes clinically significant only if such compression causes appreciable hemodynamic changes in venous flow or venous pressure, or if it leads to acute or chronic deep venous thrombosis, which will be discussed in more detail below. In addition to the other problems associated with compression, the vein may also develop intraluminal fibrous spurs from the effects of the chronic pulsatile compressive force from the overlying artery.

The narrowed, turbulent channel associated with May-Thurner syndrome may predispose the afflicted patient to thrombosis. And, the compromised blood flow often causes collateral blood vessels to form—most often horizontal transpelvis collaterals, connecting both internal iliac veins to create additional outflow possibilities through the right common iliac vein. Sometimes vertical collaterals are formed, most often paralumbar, which can cause neurological symptoms, like tingling and numbness.

Current best practices for the treatment and/or management of May-Thurner syndrome is proportional to the severity of the clinical presentation. Leg swelling and pain is best evaluated by vascular specialists, such as vascular surgeons, interventional cardiologists, and interventional radiologists, who both diagnose and treat arterial and venous diseases to ensure that the cause of the extremity pain is evaluated. Diagnosis of May-Thurner syndrome is generally confirmed one or more imaging modalities that may include magnetic resonance venography, and venogram, which, because the collapsed/flattened left common iliac may not be visible or noticed using conventional venography, are usually confirmed with intravascular ultrasound. To prevent prolonged swelling or pain as downstream consequences of the left common iliac hemostasis, blood flow out of the leg should be improved/increased. Early-stage or uncomplicated cases may be managed simply with compression stockings. Late-stage or severe May-Thurner syndrome may require thrombolysis if there is a recent onset of thrombosis, followed by angioplasty and stenting of the iliac vein after confirming the diagnosis with a venogram or an intravascular ultrasound. A stent may be used to support the area from further compression following angioplasty. However, currently available stenting options suffer from several complications—including severe foreshortenting, lack of flexibility (which can force the vessel to straighten excessively), vessel wear and eventual performation, increased load on and deformation of the stent causing early fatigue failure, and/or impedance of flow in the overlying left iliac artery potentially causing peripheral arterial disease. The compressed, narrowed outflow channel present in May-Thurner syndrome may cause stasis of the blood, which an important contributing factor to deep vein thrombosis.

Some patients suffering from May-Thurner syndrome may exhibit thrombosis while others may not. Nevertheless, those patients that do not experience thrombotic symptoms may still experience thrombosis at any time. If a patient has extensive thrombosis, pharmacologic and/or mechanical (i.e., pharmacomechanical) thrombectomy may be necessary. The hemostasis caused by May-Thurner syndrome has been positively linked to an increased incidence of deep vein thrombosis (“DVT”).

Deep vein thrombosis, or deep venous thrombosis, is the formation of a blood clot (thrombus) within a deep vein, predominantly in the legs. The right and left common iliac are common locations for deep vein thrombosis, but other locations of occurrence are common. Non-specific symptoms associated with the condition may include pain, swelling, redness, warmness, and engorged superficial veins. Pulmonary embolism, a potentially life-threatening complication of deep vein thrombosis, is caused by the detachment of a partial or complete thrombus that travels to the lungs. Post-thrombotic syndrome, another long-term complication associated with deep venous thrombosis, is a medical condition caused by a reduction in the return of venous blood to the heart and can include the symptoms of chronic leg pain, swelling, redness, and ulcers or sores.

Deep vein thrombosis formation typically begins inside the valves of the calf veins, where the blood is relatively oxygen deprived, which activates certain biochemical pathways. Several medical conditions increase the risk for deep vein thrombosis, including cancer, trauma, and antiphospholipid syndrome. Other risk factors include older age, surgery, immobilization (e.g., as experienced with bed rest, orthopedic casts, and sitting on long flights), combined oral contraceptives, pregnancy, the postnatal period, and genetic factors. Those genetic factors include deficiencies with antithrombin, protein C, and protein S, the mutation of Factor V Leiden, and the property of having a non-O blood type. The rate of new cases of deep vein thrombosis increases dramatically from childhood to old age; in adulthood, about 1 in 1000 adults develops the condition annually.

Common symptoms of deep vein thrombosis include pain or tenderness, swelling, warmth, redness or discoloration, and distention of surface veins, although about half of those with the condition have no symptoms. Signs and symptoms alone are not sufficiently sensitive or specific to make a diagnosis, but when considered in conjunction with known risk factors can help determine the likelihood of deep vein thrombosis. Deep vein thrombosis is frequently ruled out as a diagnosis after patient evaluation: the suspected symptoms are more often due to other, unrelated causes, such as cellulitis, Baker's cyst, musculoskeletal injury, or lymphedema. Other differential diagnoses include hematoma, tumors, venous or arterial aneurysms, and connective tissue disorders.

Anticoagulation, which prevents further coagulation but does not act directly on existing clots, is the standard treatment for deep vein thrombosis. Other, potentially adjunct, therapies/treatments may include compression stockings, selective movement and/or stretching, inferior vena cava filters, thrombolysis, and thrombectomy.

In any case, treatment of various venous maladies, including those described above, can be improved with stents. Improvements in stents for venous use are therefore desired.

BRIEF SUMMARY OF THE INVENTION

Accordingly, the present invention is directed to an intravascular stent that obviates one or more of the problems due to limitations and disadvantages of the related art.

In an aspect of the present invention, a stent comprises a first stent segment, the first stent segment having a first radial force RF1 and a first diameter D1; and a second stent segment, the second stent segment having a first radial force RF2 and a second diameter D2; wherein RF1>RF2.

In another aspect of the present invention, a stent system comprises a first stent, comprising a first stent segment, the first stent segment having a radial force RF1 and a diameter D1; and a second stent segment, the second stent segment having a radial force RF2 and a diameter D2; wherein RF1>RF2; an additional stent having a radial force RF4, the additional stent having an end region configured to overlap a portion of the second stent segment in vivo.

Another embodiment includes a method of delivering the stent having a first segment having a first radial for RF1 and a first diameter D1 and a second segment having a second radial force RF2 and a second diameter D2. The method includes crimping a stent onto a catheter including radially compressing and lengthening a plurality of rings connected by flexible connectors; placing the first segment at a target location and expanding the first segment and subsequently placing the second segment and expanding the second segment wherein RF1>RF2.

Further embodiments, features, and advantages of the intravascular stent, as well as the structure and operation of the various embodiments of the intravascular stent, are described in detail below with reference to the accompanying drawings.

It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only, and are not restrictive of the invention as claimed.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying figures, which are incorporated herein and form part of the specification, illustrate an intravascular stent. Together with the description, the figures further serve to explain the principles of the intravascular stent described herein and thereby enable a person skilled in the pertinent art to make and use the intravascular stent.

FIG. 1 shows an inferior-posterior view of the L5 lumbar and the bifurcations of the abdominal aorta and inferior vena cava;

FIG. 2 shows a schematic of the standard overlap of the right common iliac artery over the left common iliac vein;

FIG. 3 shows a cross-sectional schematic of the arterio-venous system shown in FIG. 2;

FIG. 4 illustrates radial force as radial resistive force or chronic outward force;

FIG. 5 illustrates crush resistance force and load on an exemplary stent;

FIG. 6 illustrates an exemplary hybrid stent according to principles of the present disclosure;

FIG. 7 illustrates an exemplary reinforcement ring according to principles of the present disclosure;

FIG. 8 illustrates an exemplary embodiment of a hybrid stent according to principles of the present disclosure;

FIG. 9A, FIG. 9B and FIG. 9C illustrate-details of the embodiment of FIG. 8.

FIG. 10 illustrates an exemplary placement of a hybrid stent according to principles of the present disclosure in the left common iliac vein;

FIG. 11 illustrates an exemplary placement of a hybrid stent having a flared end according to principles of the present disclosure in the left common iliac vein;

FIG. 12 illustrates an exemplary extension stent according principles of the present disclosure;

FIG. 13 illustrates an embodiment of an extension stent according to principles of the present disclosure; and

FIG. 14 illustrates an exemplary placement of a hybrid stent and an extension stent according to principles of the present disclosure in the left common iliac vein.

DETAILED DESCRIPTION

Accurate placement is ideal in all medical interventions, but it is vital in areas where the end that is first deployed is critical. Such areas include at vessel bifurcations and branch vessels, so that the implant does not enter or interfere with the portion of the vessel that does not require treatment. Such a bifurcation is present at the inferior vena cava where it branches into right and left iliac veins, as described in more detail below.

May-Thurner syndrome, or iliac vein compression syndrome, occurs in the peripheral venous system when the iliac artery compresses the iliac vein against the spine as shown in FIG. 1. FIG. 1 illustrates a vertebra, the right and left common iliac arteries near the bifurcation of the abdominal aorta, and the right and left common iliac arteries near the bifurcation of the inferior vena cava. The bifurcations generally occur near the L5 lumbar vertebra. Thus, it can be seen that FIG. 1 shows an inferior-posterior view of the L5 lumbar and the bifurcations of the abdominal aorta and inferior vena cava.

As shown, the strong right common iliac artery has compressed the iliac vein causing it to become narrowed. This is one possible, if not a classic, manifestation of May-Thurner syndrome. Over time, such narrowing may cause vascular scarring which can result in intraluminal changes that could precipitate iliofemoral venous outflow obstruction and/or deep vein thrombosis. As discussed above, venous insufficiency (i.e., a condition in which the flow of blood through the veins is impaired) can ultimately lead to various deleterious pathologies including, but not limited to, pain, swelling, edema, skin changes, and ulcerations. Venous insufficiency is typically brought on by venous hypertension that develops as a result of persistent venous obstruction and incompetent (or subcompetent) venous valves. Current treatments for venous outflow obstruction include anticoagulation, thrombolysis, balloon angioplasty and stenting.

FIG. 2 illustrates the standard overlap of the right common iliac artery over the left common iliac vein. The arteries shown include the abdominal aorta 1500 branching into the left common iliac artery 1501 and the right common iliac artery 1502. The veins shown include the inferior vena cava 1503 branching into the left common iliac vein 1504 and right common iliac vein 1505. It will be understood that the rough diagram illustrated in FIG. 2 represents the view looking down on a patient laying face-up (i.e., an anterior-poster view of the patient at the location of the bifurcation of the abdominal aorta 1500 and the inferior vena cava 1503). The overlap of the right common iliac artery 1502, which is relatively strong and muscular, over the left common iliac vein 1504 can cause May-Thurner syndrome by pressing down on the vein 1504, crushing it against the spine, restricting flow, and, eventually, causing thrombosis and potentially partially or completely clotting off of the left common iliac vein 1504 and everything upstream of it (i.e., the venous system in the left leg, among others).

FIG. 3 illustrates a cross-section of the arterio-venous system shown in FIG. 2 taken along the gray dotted line. Shown in schematic are the right common iliac artery 1600, the left common iliac vein 1601, and a vertebra 1602 of the spine (possibly the L5 lumbar vertebra of the lumbar spine). As can be seen, the right common iliac artery 1600 is substantially cylindrical, due to its strong, muscular construction (among other potential factors). That strong, muscular artery has pressed down on the left common iliac vein 1601, until it has almost completely lost patency, i.e., it is nearly completely pinched off. It will be understood that May-Thurner syndrome may indeed involve such severe pinching/crushing of the underlying left common iliac vein 1601 against the vertebra 1602 of the lumbar spine. However, it will also be understood that May-Thurner syndrome may involve much less pinching/crushing of the underlying left common iliac vein 1601 against the vertebra 1602. Indeed, embodiments disclosed herein are appropriate for the treatment of various degrees of May-Thurner syndrome, including full crushing/pinching of the left common iliac vein 1602 by the right common iliac artery 1600. Other embodiments disclosed herein are appropriate for the treatment of various degrees of May-Thurner syndrome, including, but not limited to a crush/pinch of the underlying left common iliac vein 1601 of between about 10-95%, about 15-90%, about 20-85%, about 25-80%, about 30-75%, about 35-70%, about 40-65%, about 45-60%, and about 50-55%, or any other crush/pinch that could merit treatment using one or more of the devices disclosed herein.

Generally, disclosed herein are stents that include circumferential rings of alternating interconnected struts connected by flexible connectors. The stent may have open or closed cells of various configuration formed by an expandable material. The final expanded implanted configuration can be achieved through mechanical expansion/actuation (e.g., balloon-expandable) or self-expansion (e.g., Nitinol). An exemplary embodiment of the stents described herein are self-expanding implants comprising super elastic or shape memory alloy materials, but the stent is not so limited and may be formed of balloon-expandable material. According to an aspect of the present disclosure, an expandable stent has varying magnitudes of radial force, crush resistance and flexibility at different locations along the length of the stent, while at the same time, the different locations have the same or similar diameter in an expanded configuration of the stent.

As illustrated in FIG. 6, an exemplary stent 10 includes a high radial force segment 14, a highly flexible segment 18 and a transition segment 22 between the high radial force segment 14 and the highly flexible segment 18. The exemplary stent 10, as illustrated in FIG. 6, may include a reinforcement ring 26 at an end of the stent 10, for example, adjacent the highly flexible segment 18 (configuration shown) or adjacent the high radial force segment 14 (configuration not shown). In an embodiment according to principles described herein, the stent 10 having a high radial force segment 14 and a highly flexible segment 18 may be cut from a single tube, such as nitinol, for example, but could also be formed or cut from flat sheets that are welded together at long edges to form a tube-like structure. While a transition segment is illustrated herein, it should be noted that a hybrid stent that does not include a transition segment is considered to be within the scope of this disclosure.

Generally radial force refers to both or either Radial Resistive Force (RRF) and Chronic Outward Force (COF). As shown in FIG. 4, radial resistive force is an external force that acts around the circumference of a stent on the stent (toward the center of the stent). Chronic outward force is the force the sent exerts outward from a direction of the center of the stent. Chronic outward force of a stent will cause the stent to exert force on the vessel in which it is inserted to resist collapse and keep the vessel open. FIG. 5 illustrates crush resistance, as used herein. Crush resistance is a force of the stent when subject to a flat plate/focal crush load. While the radial force vector directions in FIG. 6 illustrate chronic outward force, the radial force according to principles of the present disclosure may be radial resistive force, which is more related to crush resistance than a chronic outward force. Vectors illustrated in the figures are meant to indicate direction, not magnitude. Although

Radial Force and Crush Resistance can be related they do not necessarily drive each other. So a stent may be designed to have high crush resistance (flat plate/focal) but not high radial force. Such attributes can be tested independently in different test configurations.

The reinforcement ring may be an area of greater stiffness/crush resistance at an end portion of the stent. “Greater stiffness” here means having a stiffness/crush resistance greater than a portion of the stent adjacent the reinforcement ring. The reinforcement ring having greater stiffness may provide good inflow into the stent and through the vessel having the implant therein. While described herein as a “reinforcement ring,” the area of greater stiffness may be provided by an additional structure overlying the stent end (e.g., a “ring”) or may instead be an area where the strut structure is actually stronger, e.g. because the material forming the area of greater stiffness is inherently stiffer, a tighter cell structure, thicker struts or the like. For example, the reinforcement ring may have a different stent geometry, e.g., different strut width or is simply a fully-connected ring.

An exemplary embodiment of the reinforcement ring is illustrated in FIG. 7. As can be seen in FIG. 7, more of the ring struts making up the reinforcement ring are connected by flexible connectors/bridges to the adjacent ring than in the neighboring highly flexible segment.

Returning to the stent structure, as illustrated in FIG. 6, a length of stent 10 having length L0 includes high radial force segment 14 having a radial force and/or crush resistance RF1 and a flexibility F1 along the length L1 of the high radial force segment 14. That is, a radial resistive force RF1 of the high radial force segment 14 is relatively greater than the remainder of the stent 10, and may be in the range of 0.75 to 1.00 N/mm, for example. The flexibility F1 of the high radial force segment 14 may also be relatively lower than the remainder of the stent 10. Flexibility is evaluated/measured through angle of deflection. According to principles described herein, the high radial force segment may be designed to withstand long term durability (fatigue) testing with a flexion range of 0-60 degrees.

The relatively high radial force segment 14 is intended to be placed in a vessel in the region of the vessel prone to compression or crushing, such as pinching/crushing of the underlying left common iliac vein 1601 against the vertebra 1602 caused by May-Thurner syndrome, as illustrated in FIG. 3. The high radial force segment has a diameter D1.

The length of stent L0 also includes a highly flexible segment 18, which has relatively greater flexibility than the high radial force 14 segment along the length of the highly flexible segment 18. In addition, according principles of the present disclosure, the highly flexible segment 18 has a length L2, a diameter D2 and radial force, crush resistance RF2 and flexibility F2, where RF2<RF1 and F2>F1, such that the highly flexible segment is more flexible than the high radial force segment 14. According to principles described herein, the highly flexible segment may be designed to withstand long term durability (fatigue) testing with a flexion range of 0-140 degrees. A radial resistive force RF2 of the highly flexible segment 18 may be in the range of 0.50 to 0.70 N/mm, for example.

The length of stent 10 may also include a transition segment 22 between the high radial force segment 14 and the highly flexible segment 18, where the transition segment 22 has a length L3, a diameter D3 and radial force or radial resistive force (crush resistance) RF3 and flexibility F3, where RF1>RF3>RF2 and F1 and F2>F3>F1. The radial force or radial resistive force (crush resistance) RF3 and flexibility F3 of the transition segment 22 may vary over the length L3 of the transition segment 22 or may be constant along the length L3 of the transition segment 22.

Each of the high radial force segment 14, transition segment 22 and highly flexible segment 18 has a different radial force, crush resistance and flexibility, which may be provided by different ring structures in each segment of the stent 10. As can be observed in FIG. 6, a high radial force segment 14 may have a cell structure that has relatively greater periodicity, may be formed of stiffer ring struts and flexible connectors, and/or may have a more closed cell structure or other structure to impart the desired radial force or crush resistance relative to the radial force or crush resistance of the highly flexible segment. For example, the strut geometry, thicker/wider struts provide more radial strength, number of apexes around the circumference of the stent/ring geometry can all drive radial force up or down, and the configuration/connection to the adjacent rings through the bridge connectors and more ring connectors can increase radial force. Similarly, the highly flexible segment 18 may have a cell structure that has relatively lesser periodicity, may be formed of relatively more flexible ring struts and flexible connectors, and/or have a more open cell structure. The transition segment may have a cell structure that transitions a geometry of the rings struts and flexible connectors of the high radial force segment to a geometry of the highly flexible segment, or the transition segment may have a different cell structure than the high radial force segment and the highly flexible segment. In an embodiment according to principles described herein, the stent having a high radial force segment, a transition segment and a highly flexible segment may be cut from a single tube, such as nitinol, for example, but may also be formed by any other suitable means.

In the illustrated embodiment of FIG. 6, each of the segments of the stent has substantially the same diameter, such that D1≈D2≈D3. As described herein, one stent can treat a range of vein vessel diameters. The present stent structure may allow a single stent to treat multiple vessel sizes as the force exerted on the vessel remains fairly consistent over a range of diameters (3-4 mm). This is different than conventional stents in that most conventionally stents need to be specifically sized to the vessel they are treating (i.e., 0.5 mm-1.0 mm of oversizing). Thus, most conventional stents are offered in 2 mm increments (e.g., 10 mm, 12 mm, 14 mm, etc.). Adaptive diameter according to principles described herein simplifies sizing decisions for the doctor and allows a single stent to treat a long segment of vein, as the vein diameter generally reduces in diameter in the proximal direction.

It is contemplated that the length L2 of the highly flexible segment 18 will be greater than the length L1 of the high radial force segment which will be greater than the length L3 of the transition segment.

An exemplary embodiment structure of a stent 110 according to principles of the present disclosure is shown in FIG. 8. As illustrated in FIG. 8, the diameter DS along the stent 110 at any given ring 112 is substantially the same (D1≈D2≈D3). In the embodiment illustrated in FIG. 8, each of the high radial force segment (May-Thurner Syndrome “MTS” Section) 114, the transition segment (Transition Section) 122 and the highly flexible segment (Main Body Section) 118, has a similar cell pattern. In such case, the radial force or crush resistance RF of the segments may be varied by varying the thickness of the struts and/or flexible connectors 132 or the angular relationship of the struts with other struts and/or with the flexible connectors and/or the angulation of the flexible connectors themselves.

It should be noted that terms such as perpendicular, thickness, same, similar, and other dimensional and geometric terms should not be regarded as strict or perfect in their application. Instead, geometric and other dimensional reference terms should be interpreted based on their correspondence to accepted manufacturing tolerances and functional needs of the stent 110 on which they are employed. For example, the term “perpendicular” should be appreciated as affording a reasonable amount of angular variation due to manufacturing imperfections or the actual intentional curves cut or formed in the stent design 110. Also, any thickness, width or other dimension should be assessed based on tolerances and functional needs of the design rather than idealized measurements.

The thickness of the strut 128, on the other hand, is its depth in the radial direction which is generally perpendicular to the strut width measurement, as shown in FIG. 8. The strut thickness 128 normally corresponds to the wall thickness (outside diameter minus inside diameter) of the tube from which the stent 110 is laser cut after etching, grinding and other processing. But, embodiments of the stents disclosed herein are not necessarily limited to being laser-cut from a cylindrical tube with a predetermined wall thickness. They could also be formed or cut from flat sheets that are welded together at long edges to form a tube-like structure.

Each of the rings 112 is comprised of a plurality of ring struts 128 interconnected to form alternating peaks or apexes 120 and troughs 124. As shown in FIG. 8, each of the ring struts 128 is generally straight. In one embodiment shown in FIGS. 8-9, a stent 110 includes a plurality of rings 112 connected by a plurality of flexible connectors 132. The rings 112 are arranged in a spaced relationship along a long axis 116 of the stent 110. The connectors 132 extend between adjacent pairs of the rings 112. Each of the rings 112 and connectors 132 are comprised of a plurality of interconnecting struts. The dimensions and orientation of these struts are designed to provide flexibility and radial stiffness according to principles of the present disclosure.

The exemplary hybrid stent 110 illustrated in FIG. 8 may be made of Nitinol tubing that is superelastic per ASTM F2063. The stent specification may further be as follows, post eletropolishing: AF temperature of parts to be 19+/−10 degrees Celsius. The hybrid stent may be designed to treat a range of iliofemoral veins ranging in size from 12 mm to 20 mm. These dimensions are exemplary and a stent according to principles of the present disclosure are not so limited.

FIGS. 9A, 9B and 9C illustrate details of the strut and connector structure of the high radial force segment 114 (FIG. 9A) and the highly flexible segment 118 (FIG. 9B) of the embodiment FIG. 8 at the locations indicated in FIG. 8. FIG. 9C is showing detailed dimensions of the eyelet 119 geometry in which a radiopaque (RO) marker will be inserted to aid the doctor with deployment location of the stent under fluoroscopy.

FIG. 9A illustrates ring struts 128 a of the high radial force segment 114. FIG. 9B illustrates ring struts 128 b of the highly flexible segment 118.

As can be appreciated, foreshortening of the stent can be a particular problem for placement of a stent. In practice, stents with greater flexibility tend to foreshorten more. As discussed above, accurate placement is ideal in all medical interventions, but it is of great interest in areas where the end that is first deployed is critical. Such areas include at vessel bifurcations and branch vessels, so that the implant does not enter or interfere with the portion of the vessel that does not require treatment. Such a bifurcation is present at the inferior vena cava where it branches into right and left iliac veins, as described in more detail below.

As described herein, a stent according to principles described herein includes a high radial force segment and a highly flexible segment. The high radial force segment, with its stiffer structure, will foreshorten less than the highly flexible segment, and as a result, can allow for more accurate placement in the vessel into which it is implanted. FIG. 10 illustrates a rough placement of a stent according to principles of the present disclosure. FIG. 10 illustrates the inferior vena cava 1503 branching into the left common iliac vein 1504 and right common iliac vein 1505. It will be understood that the rough diagram illustrated in FIG. 10 represents the view looking down on a patient laying face-up (i.e., an anterior-poster view of the patient at the location of the bifurcation of the inferior vena cava 1503). For sake of simplicity, the abdominal aorta and its branching are not shown in FIG. 10, but are shown in FIG. 2, above.

As illustrated in FIG. 10, a multi-segment stent 10 according to principles described is placed in the left common iliac vein 1504. The high radial force segment 14 of the stent 10 may be allowed to extend into the iliac vein 1503, although the end of the high radial force segment is intended to be placed to be at the junction of the left common iliac vein 1504 and the iliac vein 1503. The highly flexible segment 18 extends away from the high radial force segment 14 and the transition segment 22 between the highly flexible segment 18 and the high radial force segment 14.

To facilitate placement of the stent 10 at the junction of the left common iliac vein 1504 and the iliac vein 1503, the stent 10 may have a flared end adjacent the high radial force segment 14, as illustrated in FIG. 11. The distal flared section is controlled by radius ‘r’. Exemplary flare sizes include 2.5 mm×5.0 mm and 5.0 mm×5.0 mm, but stent flares according to principles of the present disclosure are not so limited. The flared distal end of the stent may be used for placement of the stent at a bifurcation of two vessels such as the common iliac vein 1504 and the iliac vein 1503. The pre-loaded stent configuration on the delivery system described herein allows the distal flared section of the stent to be partially deployed from the delivery system allowing the operator to position the flared section of the stent at the bifurcation of two vessels. The delivery catheter is advanced central to the vessel bifurcation to be treated, in this case the left common iliac vein 1504. If radiopaque markers are provided on the implant, the operator can seat the partially deployed flare section of the stent at the bifurcation junction using the radiopaque markers. Once the central flared end of the partially deployed stent is in the appropriate deployment location and seated at the bifurcation junction the remainder of the stent can be deployed.

In an aspect of the present invention, a separate extension stent 50 may be included along with the stent 10. An embodiment of the separate extension stent 50 is illustrated in FIG. 12. As illustrated in FIG. 12, the separate extension stent 50 is tubular and may be a highly flexible segment similar to the highly flexible segment 18 in the hybrid stent 10 described above. In an aspect of the present disclosure, the separate extension stent 50 may comprise a plurality of rings 152, which comprise a plurality of ring struts 158 interconnected to form alternating peaks or apexes 160 and troughs 164. As shown in FIG. 12, each of the ring struts 158 is generally straight. The ring struts 158 may be connected to flexible connectors 162. The rings 152 are arranged in a spaced relationship along a long axis 116 of the stent 110. The connectors 162 extend between adjacent pairs of the rings. The separate extension stent 50 may also include reinforcement rings on either or both ends of the tube. The dimensions and orientation of these struts are designed to provide flexibility and radial stiffness according to principles of the present disclosure. Each of the rings 152 and connectors 162 comprises a plurality of interconnecting struts. The separate extension stent is made of an expandable material or a self-expandable material, such as Nitinol. The separate expansion stent 50 may be cut from a single tube, such as nitinol, for example, but could also be formed or cut from flat sheets that are welded together at long edges to form a tube-like structure.

An exemplary extension stent is illustrated in FIG. 13. The extension stent illustrated in FIG. 13 may be made of nitinol tubing that is superelastic per ASTM F2063. The stent specification may further be as follows, post electropolishing: AF temperature of parts to be 19+/−10 degrees Celsius. The extension stent may be designed to treat a range of iliofemoral veins ranging in size from 8 mm to 16 mm. These dimensions, as well as dimensions illustrated in the figures, are exemplary and a stent according to principles of the present disclosure are not so limited.

The separate extension stent 50 is placed in the left iliac vein 1504 adjacent the highly flexible segment 18 of the hybrid stent 10 and may overlap the end of hybrid stent 10, as illustrated in FIG. 14. The region of overlap in the illustration is indicted by reference number 200. The placement of the hybrid stent 10 and the separate extension stent 50 may be performed using the same delivery device at the same time. A second delivery catheter with pre-crimped extension stent may be introduced into the treatment vessel and approximate the proximal end of the previously deployed hybrid stent. The catheter with crimped extension stent would be inserted into the proximal end of the hybrid stent, positioned and the stent would be deployed utilizing the radiopaque markers on both stents to achieve appropriate overlap, e.g., 1 cm. In another aspect, the extension stent can be implanted as a stand-alone stent.

It should be noted that an extension stent as described herein may be used in combination with other stents as a “main stent”, besides the hybrid stent 10. In use, the extension stent can be used to allow for variation in placement.

In addition, the extension stent may include reinforcement rings where the reinforcement ring may be an area of greater stiffness/crush resistance at an end portion of the stent. “Greater stiffness” here means having a stiffness greater than a portion of the sent adjacent the reinforcement ring. The reinforcement ring having greater stiffness may provide good inflow into the stent and through the vessel having the implant therein. The reinforcement rings may make the extension stent easier to place with respect to the main stent, for example, by mitigating crushing of the ends as they are made to overlap. In addition, to facilitate placement, the ends of the extension stent and/or the stent to which it is to be placed adjacent can be coated with a polymer, such as urethane or PTFE. Also, the extension stent may include anchors, eyelets, radiopaque markers or other features to assist in placement of the extension stent. The extension stent may also be delivered with the main stent, or may be separately delivered to the vessel.

The extension stent may be delivered via an appropriate access site, (e.g. jugular, popliteal, etc.). The extension stent can be made to be “bidirectional”, such that it could be preloaded onto a delivery catheter without specific regard to the direction of the delivery (e.g., jugular, popliteal, etc.). E.g. the delivery can be made from above the treatment region or from below the treatment region. Such bidirectionality can be facilitated by the extensions stent geometry being symmetrical such that ends of the extension stent have the same geometry. The stent may be delivered by a coaxial delivery catheter. In another aspect of the present disclosure, a novel delivery device may include a cartridge that may be loaded onto a catheter and the hybrid sent also loaded on the catheter. The cartridge can be flipped by the operator for retrograde or anterograde. The stent may be preloaded onto the delivery catheter for the direction of the delivery (e.g., jugular, popliteal, etc.)

As can be appreciated, the actual stent ring geometry may vary from that disclosed herein, as long as the stent 10 includes a first section with a relatively higher radial force or crush resistance than a second section of the stent that has a relatively higher flexibility than the first section. It is also contemplated that the separate extension stent 50 have a flexibility similar to the highly flexible segment of the hybrid stent 10. Exemplary stent geometries for segments of the hybrid stent 10 and the extension stent 50 are taught in U.S. patent application Ser. Nos. 15/471,980 and 15/684,626, which are hereby incorporated by reference for all purposes as if fully set forth herein.

For example, it is noted that the struts of the rings and flexible connectors with structure, including areas of expanded or reduced width or thickness, to account for venous applications may be used. As another example, it is noted that venous applications benefit from configurations that improve flexibility (due to the greater elasticity of venous applications) while maintaining enough stiffness to resist pressure on the venous structure in selected areas (such as for the May-Thurner syndrome).

Notably the stents herein are not necessarily limited to venous applications unless specifically required by the claims. The disclosed stents could be employed in arterial and biliary applications, for example. But, are particularly suited for the demands of relatively soft structures defining lumens that are subject to much greater bending, twisting, stretching and other contortions and loads than are general arterial lumens.

To deploy the implant, the implant may be radially compressed/crimped to a smaller diameter for loading onto/into a delivery catheter. The implant may be crimped over a balloon on the inner core of the delivery system which may be later inflated to expand the crimped implant to the desired diameter.

Implants such as those described above may advantageously provide an adaptive diameter and/or flexibility to conform the dynamic movement of peripheral veins in leg/pelvis thereby facilitating treatment of both iliac vein compression syndrome and ilio-femoral venous outflow obstructions.

It may be desirable to have a stent that will conform to the existing path of a vein instead of a straightening out of the vessel by the stent. It may also be desirable to have a high radial stiffness of the stent to resist collapse of the stent under crushing load and to maximize the resultant diameter of the treated vessel at the location of the stent deployment. With most stent constructions there is a direct relationship between radial stiffness and axial stiffness.

Common commercially available balloon expandable stents experience a dramatic change in length as a balloon is used to expand the stent within the vessel. Common commercially available self-expanding stents experience a change in length less dramatic, but still substantial, which increases with increasing stent length. Change in length between the configuration within the delivery system and when deployed in the vessel causes difficulty in placing/landing the stent precisely at the target location. When the stent is delivered in its crimped configuration, then deployed or expanded, the shortening in length causes the stent target deployment location to have to offset from the target dwell location. The magnitude of this effect is not controllable or easily anticipated as it is dependent on the luminal cross-section along the length of the target dwell location (which is frequently and unexpectedly influenced by residual stenosis, irregular shape due to external objects, and/or forces, etc.). For target lesions leading up to the junction of the left and right iliac into the IVC, this causes difficulty in placing the stent to dwell completely within the iliac along its total length up to the junction to the inferior vena cava without crossing into the inferior vena cava. Placement of a high radial force segment at the junction not only assists in addressing crush by May-Thurner Syndrome, but also may assist in reducing foreshortening from the target location.

Embodiments disclosed herein can be used for both balloon expandable and self-expanding stent designs. The stent designs can be used for all stent interventions, including coronary, peripheral, carotid, neuro, biliary and, especially, venous applications. Additionally, this could be beneficial for stent grafts, percutaneous valves, etc.

Currently available implants are typically loaded and retained onto a delivery system in a crimped configuration and then navigated and deployed in the desired anatomical location where they expand to the implanted configuration. The final implanted configuration can be achieved through mechanical expansion/actuation (e.g., balloon-expandable) or self-expansion (e.g., Nitinol). Self-expanding implants are manufactured from super elastic or shape memory alloy materials. Accurate and precise deployment of a self-expanding implant can be challenging due to a number of inherent design attributes associated with self-expanding implants. The implant may jump/advance from the distal end of the delivery system during deployment due to the stored elastic energy of the material. Additionally, the implant may foreshorten during deployment due to the change in the implant diameter from the crimped configuration to the expanded configuration. Finally, physiological and anatomical configurations, such a placement at or near bifurcations of body lumens, can affect accurate placement of implants. Once the implant is placed within the body lumen there is potential for uneven expansion or lack of circumferential implant apposition to the body lumen which can result in movement, migration or in certain severe cases implant embolization.

In some embodiments, a self-expanding implant designed with sufficient radial force or crush resistance to resist constant compression of the body lumen while providing optimal fatigue resistance, accurate placement, and in-vivo anchoring to prevent movement/migration is provided. Additionally, various methods for deployment and implantation for treating iliac vein compression syndrome and venous insufficiency disease are provided.

In some embodiments, the implant comprises a purposely designed venous implant intended to focally treat iliac vein compression (May-Thurner Syndrome). The implant may be relatively short in length (˜60 mm) and may be manufactured from self-expending Nitinol with integrated anchor features to aid in accurate placement and to mitigate migration following implantation. The implant and delivery system are designed for precise deployment and placement at the bifurcation of the inferior vena cava into the right and left common iliac veins.

As another feature, the stents disclosed herein can include anchor members, radiopaque markers, or eyelets, for example, set forth in pending U.S. patent application Ser. Nos. 15/471,980 and 15/684,626, which are hereby incorporated by reference for all purposes as if fully set forth herein.

Although this invention has been disclosed in the context of certain preferred embodiments and examples, it will be understood by those skilled in the art that the present invention extends beyond the specifically disclosed embodiments to other alternative embodiments and/or uses of the invention and obvious modifications and equivalents thereof. In addition, while a number of variations of the invention have been shown and described in detail, other modifications, which are within the scope of this invention, will be readily apparent to those of skill in the art based upon this disclosure. It is also contemplated that various combinations or sub-combinations of the specific features and aspects of the embodiments may be made and still fall within the scope of the invention. Accordingly, it should be understood that various features and aspects of the disclosed embodiments can be combined with or substituted for one another in order to form varying modes of the disclosed invention. Thus, it is intended that the scope of the present invention herein disclosed should not be limited by the particular disclosed embodiments described above, but should be determined only by a fair reading of the claims that follow.

Similarly, this method of disclosure, is not to be interpreted as reflecting an intention that any claim require more features than are expressly recited in that claim. Rather, as the following claims reflect, inventive aspects lie in a combination of fewer than all features of any single foregoing disclosed embodiment. Thus, the claims following the Detailed Description are hereby expressly incorporated into this Detailed Description, with each claim standing on its own as a separate embodiment.

While various embodiments of the present invention have been described above, it should be understood that they have been presented by way of example only, and not limitation. It will be apparent to persons skilled in the relevant art that various changes in form and detail can be made therein without departing from the spirit and scope of the present invention. Thus, the breadth and scope of the present invention should not be limited by any of the above-described exemplary embodiments, but should be defined only in accordance with the following claims and their equivalents. 

What is claimed is:
 1. A stent comprising: a stent tube having stent tube length L0, the stent tube comprising: a high radial force segment having a first radial force RF1 having a vector parallel to a radial direction of the stent tube, a first flexibility F1, whereby two points along a surface of the tube in an axial direction are moveable toward each other, and a length L1; wherein first radial force R1 is a vector measure of forces in a direction parallel to a radial direction of the stent tube in length L1; and wherein first flexibility F1 is measure of movability of two points along a surface of the tube in an axial direction of length L1 toward each other; and a highly flexible segment having a second radial force RF2, a second flexibility F2 and a length L2; wherein second radial force R2 is a vector measure of forces in a direction parallel to a radial direction of the stent tube in length L2; and wherein second flexibility F2 is measure of movability of two points along a surface of the tube in an axial direction of length L2 toward each other; wherein the stent tube length includes length L1 and length L2, where L2>L1; wherein RF1>RF2; and F1<F2, and wherein first radial force RF1 is independent of first flexibility F1 and second radial force RF2 is independent of second flexibility F2.
 2. The stent of claim 1, wherein the high radial force segment comprises a plurality of contiguous interconnected struts and the highly flexible segment comprises a plurality of contiguous interconnected struts.
 3. The stent of claim 2, wherein the high radial force segment has a proximal end and a distal end and the highly flexible region has a proximal end and a distal end, wherein the distal end of the high radial force segment is contiguous with the proximal end of the highly flexible segment.
 4. The stent of claim 3, further comprising a reinforcement ring at least one of the proximal end of the high radial force segment and the distal end of the highly flexible segment.
 5. The stent of claim 3, wherein the proximal segment of the high radial force segment has a flare shape.
 6. The stent of claim 1, wherein the high radial force segment and the highly flexible segment comprises a single unitary tube.
 7. The stent of claim 1, wherein the high radial force segment has a diameter D1 in an expanded state and the highly flexible segment has a diameter D2 in an expanded state, and D1=D2 in an expanded state.
 8. The stent of claim 1, wherein the first radial force RF1 is radial resistive force (ROF) and the second radial force RF2 is radial resistive force (ROF).
 9. The stent of claim 1, wherein the first radial force RF1 is chronic outward force (COF) and the second radial force RF2 is chronic outward force (COF).
 10. The stent of claim 1, further comprising an additional stent segment, unconnected to the stent tube, the additional stent segment having an end region configured to overlap a portion of the highly flexible segment in vivo.
 11. A stent comprising: a stent tube having stent tube length L0, the stent tube comprising: a high radial force segment having a first radial force RF1, a first flexibility F1 and a length L1; wherein first radial force R1 is a vector measure of forces in a direction parallel to a radial direction of the stent tube in length L1; and wherein first flexibility F1 is measure of movability of two points along a surface of the tube in an axial direction of length L1 toward each other; a highly flexible segment having a second radial force RF2, a second flexibility F2 and a length L2; wherein second radial force R2 is a vector measure of forces in a direction parallel to a radial direction of the stent tube in length L2; and wherein second flexibility F2 is measure of movability of two points along a surface of the tube in an axial direction of length L2 toward each other; and a transition segment between the high radial force segment and the highly flexible segment and having a third radial force RF3, a third flexibility F3 and a length L3; wherein the stent tube length includes length L1 and length L2, where L2>L1; wherein third radial force R3 is a vector measure of forces in a direction parallel to a radial direction of the stent tube in length L3; and wherein third flexibility F3 is measure of movability of two points along a surface of the tube in an axial direction of length L3 toward each other wherein RF1>RF3>RF2 and F1<F3<F2; and wherein first radial force RF1 is independent of first flexibility F1, second radial force RF2 is independent of second flexibility F2; and third radial force RF3 is independent of third flexibility F3.
 12. The stent of claim 11, wherein the third radial force RF3 varies along the length L3 of the transition segment.
 13. The stent of claim 11, wherein the third flexibility F3 varies along the length L3 of the transition segment.
 14. The stent of claim 11, wherein the third radial force RF3 is constant along the length L3 of the transition segment.
 15. The stent of claim 11, wherein the third flexibility F3 is constant along the length L3 of the transition segment.
 16. The stent of claim 11, wherein the high radial force segment comprises a first plurality of contiguous interconnected struts, the highly flexible segment comprises a second plurality of contiguous interconnected struts, and the transition segment comprises a third plurality of interconnected struts.
 17. The stent of claim 16, wherein the high radial force segment has a proximal end and a distal end, the highly flexible region has a proximal end and a distal end, and the transition segment has a proximal end and a distal end, wherein the distal end of the high radial force segment is contiguous with the proximal end of the transition segment and the distal end of the transition segment is contiguous with the proximal end of the highly flexible segment.
 18. The stent of claim 17, further comprising a reinforcement ring at least one of the proximal end of the high radial force segment and the distal end of the highly flexible segment.
 19. The stent of claim 17, wherein the proximal segment of the high radial force segment has a flare shape.
 20. The stent of claim 11, wherein the high radial force segment, the transition segment and the highly flexible segment comprises a single unitary tube.
 21. The stent of claim 11, wherein the high radial force segment has a diameter D1 in an expanded state, the highly flexible segment has a diameter D2 in an expanded state, the transition segment has a diameter D3, and D1=D2=D3 in an expanded state.
 22. The stent of claim 11, wherein the first radial force RF1 is radial resistive force (ROF), the second radial force RF2 is radial resistive force (ROF) and the third radial force R3 is radial resistive force (ROF).
 23. The stent of claim 11, wherein the first radial force RF1 is chronic outward force (COF), the second radial force RF2 is chronic outward force (COF), and the third radial force RF3 is chronic outward force (COF).
 24. The stent of claim 11, further comprising an additional stent segment, unconnected to the stent tube, the additional stent segment having an end region configured to overlap a portion of the highly flexible segment in vivo. 